|Publication number||US4934381 A|
|Application number||US 06/711,759|
|Publication date||Jun 19, 1990|
|Filing date||Mar 14, 1985|
|Priority date||May 9, 1975|
|Publication number||06711759, 711759, US 4934381 A, US 4934381A, US-A-4934381, US4934381 A, US4934381A|
|Inventors||David C. MacGregor|
|Original Assignee||Macgregor David C|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (8), Referenced by (26), Classifications (27), Legal Events (6)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application is a continuation of Ser. No. 375,442 filed May 6, 1982 (now abandoned), which itself is a continuation-in-part of U.S. patent application Ser. No. 226,366 filed Jan. 19, 1981 (now abandoned), which is a continuation of U.S. patent application Ser. No. 824,296 filed Aug. 15, 1977 (now U.S. Pat. No. 4,281,669) which itself is a continuation-in-part of U.S. patent application Ser. No. 683,382 filed May 5, 1976 (now U.S. Pat. No. 4,101,984).
The present invention relates to pacemaker electrodes.
Three major problems which may be encountered with endocardial pacemaker electrodes during use are (1) a lack of stable position, (2) a chronic increase in stimulation threshold, and (3) a diminishing magnitude of the sensed endocardial signal. These problems are particularly manifested in the atrium, where maintenance of a stable anatomical position of the electrode has been a particularly difficult problem in the development of satisfactory endocardial leads for atrial pacing.
Another problem which is manifested in the blood stream by polished metal surfaces, such as are typically used in pacemaker electrodes, is the tendency to cause the formation of blood clots which may break loose and emobolize to various parts of the body.
In accordance with the present invention, there is provided an endocardial heart pacemaker electrode having a porous surface to permit tissue to form in the pores and at the surface thereof with a resulting tissue bond to the adjacent endocardium, thereby achieving a stable position of the electrode tip. In addition, the tissue formed at the surface provides a thin tissue covering on the exposed surface to render the same resistant to the formation of blood clots.
The fixation of the electrode in the atrium by tissue formation overcomes the problems of maintenance of a stable anatomical position characteristic of the prior art and enables low stimulation thresholds and a consistent magnitude of the sensed endocardial signal to be maintained.
The formation of the tissue coating on the exposed portions of the electrode surface with the consequent resistance of the surface to the formation of blood clots overcomes another difficulty of the prior art.
The electrode of the present invention is primarily designed for endocardial use for atrial pacemaking and is described with particular reference thereto. The electrode of the present invention, however, may also be used for endocardial ventricular or coronary sinus pacing.
The surface of the heart pacemaker electrode of this invention which engages the tissue is constructed of carbon. The electrode may be constructed wholly of carbon with the porous surface formed as an integral part thereof, or may be a composite of materials providing the carbon surface.
Carbon is an excellent conductor of electricity and is substantially inert to soft tissue, so that little or no reaction to the electrode occurs. These properties make carbon an excellent choice as the material of construction of a pacemaker electrode.
The combination of the physical attributes of the use of a carbon surface and the maintenance of a stable anatomical position by the use of the porous surface produces an implantable pacemaker electrode of superior properties.
FIG. 1 is a part sectional view of a heart pacemaker electrode constructed in accordance with one embodiment of the invention;
FIG. 2 is a part sectional view of a heart pacemaker electrode constructed in accordance with a second embodiment of the invention;
FIG. 3 is a part sectional view of a heart pacemaker electrode constructed in accordance with a third embodiment of the invention.
In accordance with the present invention, it is essential that the electrode have a porous surface region constructed of carbon which permits tissue to form in the pores and bind the electrode to the endocardium or other adjacent tissue surface. The carbon may be in a native or activated form.
The porosity in the surface region may be provided in any convenient manner. For example, a plurality of pores may be formed in a solid carbon electrode, for example, by microfine drilling.
In another embodiment of the invention, the porous surface region may be provided by a fabric material, which is constructed of, impregnated with or coated with carbon material, bonded to a substrate.
The porous surface region may be in the form of carbon particles integrally joined into a matrix of interconnected pores with which the ingrowing tissue may interlock. Such a matrix of carbon particles may be bonded to or be integrally formed with a solid substrate of carbon or other material, or may constitute the electrode, whereby the electrode is wholly porous.
Such a matrix structure may be formed in any convenient manner, such as by pyrolyzing particles of a carbon precursor material, by sputtering, by plasma coating or by vapor deposition.
The pacemaker electrode of the invention may have any desired geometrical configuration conventional for pacemaker electrodes. For example, the electrode may have a cylindrical shape, in which case the overall length of the pacemaker electrode of the invention usually is about 0.1 to about 3 mm, preferably about 1 mm, and the diameter usually is also about 0.5 to about 5 mm, preferably about 2 mm. Such cylindrical electrodes may contain an insulating plug, usually of diameter of about 0.5 to about 3 mm, in the end thereof, which decreases the overall surface area of the electrode and is desirable under certain circumstances.
The electrode also may have a spherical shape, usually of diameter of about 0.5 to about 5 mm, preferably about 2 mm. The electrode may also include a cylindrical electrode sleeve positioned remote from the end of the lead, and may be used alone or in combination with a tip electrode. The electrode sleeve usually has an outside diameter of about 1 to about 5 mm, a thin wall usually of thickness of about 0.05 to about 0.3 mm, and a length of about 1 to about 10 mm, preferably about 3 mm.
The pore size of the pores in the porous surface of the electrode may vary widely but must be large enough to permit the growth of soft tissue into the pores and must be not so large that structural integrity is lost under the physiological stress of the body environment in which the electrode is located. Usually, the pore size of the pores is less than about 200 microns, preferably about 20 to about 100 microns.
As noted above, it is preferred that the porous surface be in communication with a network of interconnected pores in a subsurface. In such structure, the interstitial pore size is usually the same as the surface pore size while the porosity usually is about 10 to about 50% by volume.
The electrode may comprise a porous coating on a solid substrate. In such structure, the porous coating usually has a thickness of less than about 500 microns, preferably about 20 to about 300 microns.
The engagement of the porous surface region of the electrode with the blood stream in the atrium results in a controlled thrombotic reaction in which blood elements, including erythrocytes, platelets and leukocytes, accumulate in the pores and on the surface of the coating. Subsequent organization of the thrombus tissue, when in contact with the endocardium, results in the development of fibrous tissue within the pores and on the surface of the electrode with a resulting tissue bond to adjacent endocardium. This fibrous tissue is partially formed by colonization of nucleated cells circulating in the bloodstream onto the exposed porous surface and subsequent differentiation into other cell types which include fibrocytes, as well as direct ingrowth from the tissue in direct contact with the electrode.
The exposed portions of the porous surface of the electrode not in contact with the endocardium promotes the formation of a smooth, thin, adherent tissue covering on the porous surface, thereby rendering the same resistant to the formation of blood clots. The tissue coating is formed rapidly over a one to three month period and does not appear to increase significantly in thickness thereafter. This tissue response also represents organization of thrombus resulting in fibrous tissue formation within the pores and on the porous surface but the blood-contacting tissue consists of flattened endothelial-like cells which confer thromboresistance.
The formation of the fibrous tissue in the porous surface of the electrode with the consequent tissue bond to the endocardium fixedly locates the same in close proximity to the underlying myocytes, enabling consistently low chronic stimulation thresholds and a consistent magnitude of the sensed enocardial signal to be maintained. This result contrasts markedly with conventional leads which have smooth metal tips. The lack of stable fixation to the endocardium causes a tissue reaction and the formation of a thick tissue layer on the endocardium, widely separating the electrode from the myocardium, thereby causing an increase in stimulation threshold and decreased sensed endocardial signal during use.
Referring to the drawing, a pacemaker electrode 10 has a generally cylindrical shape and comprises a coherent substrate 12 and a porous carbon coating 14 adhered thereto.
In FIG. 2, a pacemaker electrode 20 has a spherical shape and comprises a coherent substrate 22 and a porous carbon coating 24 adhered thereto. Similarly, in FIG. 3, a pacemaker electrode 30 has an elongate body 32, a cylindrical sleeve 34 mounted on the body and a porous carbon coating 36 adhered thereto.
In summary of this disclosure, the present invention provides a pacemaker electrode of improved construction. Modifications are possible within the scope of this invention.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3590822 *||Apr 3, 1968||Jul 6, 1971||Electro Catheter Corp||Catheters|
|US3757789 *||Oct 26, 1971||Sep 11, 1973||Shanker I||Electromedical stimulator lead connector|
|US3855638 *||May 16, 1973||Dec 24, 1974||Ontario Research Foundation||Surgical prosthetic device with porous metal coating|
|US4011861 *||Oct 28, 1975||Mar 15, 1977||Case Western Reserve University||Implantable electric terminal for organic tissue|
|US4030508 *||Feb 4, 1976||Jun 21, 1977||Vitatron Medical B.V.||Low output electrode for cardiac pacing|
|US4052754 *||Jul 14, 1976||Oct 11, 1977||Homsy Charles A||Implantable structure|
|US4149542 *||Jan 28, 1977||Apr 17, 1979||Siemens Aktiengesellschaft||Endocardial electrode|
|US4281668 *||Sep 21, 1979||Aug 4, 1981||Siemens Aktiengesellschaft||Implantable carbon electrode|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US5097843 *||Apr 10, 1990||Mar 24, 1992||Siemens-Pacesetter, Inc.||Porous electrode for a pacemaker|
|US5118400 *||Jan 29, 1990||Jun 2, 1992||Spire Corporation||Method of making biocompatible electrodes|
|US5228407 *||Feb 1, 1991||Jul 20, 1993||Barry Douglas Enterprises Ltd.||Rigid inflatable boat|
|US5282844 *||May 18, 1992||Feb 1, 1994||Medtronic, Inc.||High impedance, low polarization, low threshold miniature steriod eluting pacing lead electrodes|
|US5318572 *||Jun 2, 1992||Jun 7, 1994||Siemens Pacesetter, Inc.||High efficiency tissue stimulating and signal sensing electrode|
|US5408744 *||Apr 30, 1993||Apr 25, 1995||Medtronic, Inc.||Substrate for a sintered electrode|
|US5922014 *||Sep 2, 1997||Jul 13, 1999||Medtronic, Inc.||Single pass lead and method of use|
|US5991667 *||Nov 10, 1997||Nov 23, 1999||Vitatron Medical, B.V.||Pacing lead with porous electrode for stable low threshold high impedance pacing|
|US6021354 *||Dec 31, 1998||Feb 1, 2000||Medtronic, Inc.||Single pass lead and method of use|
|US6201994||Nov 30, 1999||Mar 13, 2001||Medtronic, Inc.||Single pass lead and method of use|
|US6405078||Aug 10, 1999||Jun 11, 2002||Biosense Webster, Inc.||Porous irrigated tip electrode catheter|
|US6466818||Aug 10, 1999||Oct 15, 2002||Biosense Webster, Inc.||Porous irrigated tip electrode catheter|
|US6671560||Feb 20, 2002||Dec 30, 2003||Cardiac Pacemakers, Inc.||Modified guidewire for left ventricular access lead|
|US6901288||Oct 2, 2001||May 31, 2005||Cardiac Pacemakers, Inc.||Sealing assembly for intravenous lead|
|US7079903||Mar 3, 2004||Jul 18, 2006||Greatbatch-Hittman, Inc.||Low polarization coatings for implantable electrodes|
|US7412290||Oct 20, 2004||Aug 12, 2008||Cardiac Pacemakers, Inc.||Seal for use with medical device and system|
|US7657324||Jul 14, 2003||Feb 2, 2010||Cardiac Pacemakers, Inc.||Seal for use with cardiac lead|
|US8066770 *||Dec 20, 2007||Nov 29, 2011||Depuy Products, Inc.||Sintered coatings for implantable prostheses|
|US20040176828 *||Mar 3, 2004||Sep 9, 2004||O'brien Robert C.||Low polarization coatings for implantable electrodes|
|US20050085885 *||Oct 20, 2004||Apr 21, 2005||Cardiac Pacemakers, Inc.||Expandable seal for use with medical device and system|
|US20070123923 *||Nov 30, 2005||May 31, 2007||Lindstrom Curtis C||Implantable medical device minimizing rotation and dislocation|
|US20080300682 *||Dec 20, 2007||Dec 4, 2008||Depuy Products, Inc.||Sintered Coatings For Implantable Prostheses|
|DE4112936A1 *||Apr 17, 1991||Oct 24, 1991||Biotronik Mess & Therapieg||Electrode esp. for heart pacemaker - has non-conductive tip coated with conductive coating|
|EP0813885A2 *||Jun 12, 1997||Dec 29, 1997||SORIN BIOMEDICA CARDIO S.p.A.||An electrode for biomedical use, for example, for cardiac stimulation|
|EP0813885A3 *||Jun 12, 1997||Oct 20, 1999||SORIN BIOMEDICA CARDIO S.p.A.||An electrode for biomedical use, for example, for cardiac stimulation|
|WO1991019533A1 *||Jun 11, 1991||Dec 26, 1991||Medtronic, Inc.||Miniature steroid eluting pacing lead electrode|
|International Classification||A61F2/06, A61F2/00, A61L33/02, A61N1/05, A61L27/56, A61L27/14, A61L27/34, A61L27/18|
|Cooperative Classification||A61N1/0565, A61L27/18, A61N1/05, A61L27/14, A61L27/56, A61F2/0077, A61L33/022, A61L27/34, A61F2/06|
|European Classification||A61L27/18, A61L27/34, A61F2/06, A61L27/56, A61N1/05N2, A61L27/14, A61L33/02B, A61N1/05, A61F2/00L|
|Sep 13, 1993||AS||Assignment|
Owner name: TELECTRONICS PACING SYSTEMS, INC., COLORADO
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:ORTECH CORPORATION;REEL/FRAME:006689/0141
Effective date: 19921218
|Nov 15, 1993||FPAY||Fee payment|
Year of fee payment: 4
|Mar 21, 1997||AS||Assignment|
Owner name: PACESETTER, INC., CALIFORNIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:TELECTRONICS PACING SYSTEMS;REEL/FRAME:008454/0461
Effective date: 19961129
|Dec 4, 1997||FPAY||Fee payment|
Year of fee payment: 8
|Dec 18, 2001||FPAY||Fee payment|
Year of fee payment: 12
|Jan 9, 2002||REMI||Maintenance fee reminder mailed|